JP2012505707A - Neurophysiological monitoring system and related methods - Google Patents

Abstract

  The present invention relates generally to systems and methods directed to surgery. More specifically, the present invention is directed to systems and related methods for performing assessments involving the use of surgical procedures and neurophysiology.

Description

CROSS REFERENCE TO RELATED APPLICATIONS This application is entitled "Neurophysic Monitoring System" and is the priority of co-owned and co-pending US Provisional Application No. 61 / 196,264, filed October 14, 2008. International patent application claiming benefit, the entire contents of which are hereby expressly incorporated by reference into the present disclosure as if fully set forth herein.
The present invention relates generally to systems and methods directed to surgery. More specifically, the present invention is directed to systems and related methods for performing surgical procedures and evaluations that involve the use of neurophysiological recordings.

  Neurophysiological monitoring has become increasingly important as an aid to surgical procedures in which nerve tissue can be compromised. In particular, spinal surgery involves working in close proximity to delicate tissue in and around the spine, which can be damaged in a number of different ways. For example, an outgoing nerve root may be included if the surgical instrument must pass next to or near the nerve while approaching a surgical target site in the spine. Also, spinal nerves and / or protruding nerve roots may be compromised when pedicle screws often used to secure multiple vertebrae firmly to each other cut through the cortical layers of the pedicles . Surgery targeting the spine may also require nerve and / or vascular tissue to be incised outside the surgical path. While it is necessary to do so, there is the potential for damaging nerve tissue by excessive incision and / or a reduced blood supply reaching the tissue due to invasion of the retractor to the vascular tissue. In an attempt to reduce the risks inherent in spinal surgery (and general surgery), various neurophysiological techniques for monitoring sensitive neural tissue have been attempted and developed. Due to the complex structure of the spine and nervous system, no single monitoring technique has been developed that can accurately assess the risk to nervous tissue in all situations, and in many cases one complex technique Used in conjunction with other complex monitoring techniques. EMG monitoring can be used, for example, to detect the presence of a nerve root near a surgical instrument or a cut formed in the pedicle wall. However, EMG monitoring is not as effective when spinal cord monitoring is required.

  When spinal cord monitoring is required, either motor evoked potential (MEP) monitoring or somatosensory evoked potential (SSEP) monitoring or both are often selected. While both MEP monitoring and SSEP monitoring can be very effective in detecting changes in spinal cord health, MEP has limitations because it only monitors the anterior column of the spinal cord, and SSEP Because it only monitors the spinal column, there are limitations. The risk to neural tissue that can be detected using one of these methods can be missed by the other, and vice versa. Thus, it may be most effective to use both MEP and SSEP monitoring during the same procedure, while still requiring EMG monitoring in some cases.

  EMG, MEP, and SSEP involve complex analysis and generally call for specially trained neurophysiologists to perform monitoring. Interpreting complex waveforms in this way, even if performed by professionals, can still be disadvantageous and prone to human error, can be disadvantageous and time consuming, increasing the duration of surgery, and as a result Increase costs. Even more expensive is the fact that in addition to the actual surgeon performing spinal surgery, a neurophysiologist is needed. In addition to the difficulties associated with human interpretation of EMG monitoring, MEP monitoring, and SSEP monitoring, combining such tests at the OR requires multiple products to accommodate each different requirement. In many cases, this is disadvantageous because in today's operating rooms, space is very scarce. The present invention aims to eliminate or at least reduce the effects of the above-mentioned problems associated with the prior art.

  The present invention includes systems and methods for avoiding injury to nerve tissue during surgery. According to a broad aspect, the present invention provides an instrument capable of stimulating a patient's peripheral nerve, a patient's spinal cord, or both, an additional instrument capable of recording an evoked somatosensory response, and a processing system. Including. The instrument is configured to deliver stimulation signals before, during and after surgery. The processing system is programmed with a set of at least three threshold ranges and is configured to receive a first stimulus signal to the instrument at a first magnitude. The first magnitude corresponds to the boundary between the pair of ranges. In addition, the processing system receives a second stimulus signal of a second magnitude that corresponds to a boundary between different pairs of ranges. Further, the processing unit is programmed to measure a neural response that is depolarized by the stimulation signal received by the somatosensory cortex to indicate spinal health.

According to another broad aspect, the present invention includes a control unit, a patient module, and a plurality of surgical aids adapted to couple to the patient module. The control unit includes a power supply, receives user commands, activates stimulation in multiple predefined modes, processes signal data according to a defined algorithm, displays received parameters and processed data And programmed to monitor system status. The patient module is in communication with the control unit. The patient module is in a sterile field. The patient module includes a signal conditioning circuit, a stimulator drive circuit, and a signal conditioning circuit required to perform the stimulation in a predetermined mode. Patient module includes static carcass integrity test, dynamic carcass integrity test, nerve proximity detection, neuromuscular pathway evaluation, manual motor evoked potential monitoring, automatic motor evoked potential monitoring, manual somatosensory evoked potential monitoring, automatic A processor that is programmed to perform a plurality of predefined functions, including at least two of motor evoked potential monitoring, non-evoked monitoring, and surgical navigation.
According to yet another broad aspect, the present invention includes an instrument and a processing system. The instrument is in communication with the processing unit. The instrument is capable of being advanced to a surgical target site and configured to deliver a stimulation signal during at least one of being advanced to the target site and reaching the target site Is done. The processing unit uses the instrument to perform static stalk integrity test, dynamic stalk integrity test, nerve proximity detection, neuromuscular path evaluation, manual motor evoked potential monitoring, automatic motor evoked potential monitoring, manual body It is programmed to perform a plurality of predefined functions including at least two of sexual sensory evoked potential monitoring, automatic somatosensory evoked potential monitoring, non-evoked monitoring, and surgical navigation. The processing system has a pre-established profile for at least one of the predefined functions to facilitate initiation of the at least one predefined function.

Many advantages of the present invention will become apparent to those skilled in the art upon reading this specification in conjunction with the accompanying drawings, in which like reference numerals apply to like elements.
Multiple nerves and spinal cord, including but not necessarily limited to manual SSEP, automatic SSEP, manual MEP, automatic MEP, neuromuscular pathway, bone integrity, nerve detection, and neuropathology (evoked or sustained EMG) assessment 1 is a block diagram of an exemplary surgical system that can perform monitoring functions. FIG. FIG. 2 is a perspective view showing an example of some components of the neurophysiology system of FIG. 1. FIG. 2 is a perspective view of an embodiment of a control unit that forms part of the neurophysiology system of FIG. 1. FIG. 2 is a perspective view, top view, and side view of an example patient module that forms part of the neurophysiology system of FIG. 1, respectively. FIG. 2 is a perspective view, top view, and side view of an example patient module that forms part of the neurophysiology system of FIG. 1, respectively. FIG. 2 is a perspective view, top view, and side view of an example patient module that forms part of the neurophysiology system of FIG. 1, respectively. FIG. 2 is a top view of an electrode harness that forms part of the neurophysiology system of FIG. 1. FIG. 2 is a side view of various embodiments of harness ports that form part of the neurophysiology system of FIG. 1. FIG. 2 is a side view of various embodiments of harness ports that form part of the neurophysiology system of FIG. 1. FIG. 2 is a side view of various embodiments of harness ports that form part of the neurophysiology system of FIG. 1. FIG. 2 is a plan view of an example of a label attached to an electrode connector that forms part of the neurophysiology system of FIG. 1. FIG. 2 is a top view of an example of an electrode cap that forms part of the neurophysiology system of FIG. 1. FIG. 2 is a top view of an example of an electrode cap that forms part of the neurophysiology system of FIG. 1. FIG. 2 is a perspective view of an example of an auxiliary display that forms part of the neurophysiology system of FIG. 1. FIG. 2 is a perspective view of an example of an auxiliary display that forms part of the neurophysiology system of FIG. 1. 2 is an exemplary screen display illustrating one embodiment of a general system settings screen that forms part of the neurophysiology system of FIG. 2 is an exemplary screen display illustrating one embodiment of a detailed profile screen that forms part of the neurophysiology system of FIG. 2 is an exemplary screen display illustrating one embodiment of a custom profile selection screen that forms part of the neurophysiology system of FIG. 2 is an exemplary screen display with an electrode test mechanism incorporated into one embodiment of an electrode test screen that forms part of the neurophysiology system of FIG. 2 is an exemplary screen display illustrating one embodiment of an SSEP profile selection screen that forms part of the neurophysiology system of FIG. 4 is an exemplary screen display illustrating a second embodiment of a manual SSEP stimulation mode setting with a left ulnar nerve (LUN) pop-up screen forming part of the neurophysiology system of FIG. 2 is an exemplary screen display illustrating one embodiment of a manual SSEP execution screen that forms part of the neurophysiology system of FIG. 4 is an exemplary screen display illustrating a second embodiment of a manual SSEP execution screen that forms part of the neurophysiology system of FIG. FIG. 4 is an exemplary screen display illustrating a third embodiment of a manual SSEP execution screen that forms part of the neurophysiology system of FIG. 6 is an exemplary screen display illustrating a fourth embodiment of a manual SSEP execution screen that forms part of the neurophysiology system of FIG. 2 is an exemplary screen display illustrating one embodiment of an automatic SSEP test setup screen that forms part of the neurophysiology system of FIG. 2 is an exemplary screen display illustrating one embodiment of an automatic SSEP execution screen that forms part of the neurophysiology system of FIG. 4 is an exemplary screen display illustrating a second embodiment of an automatic SSEP execution screen that forms part of the neurophysiology system of FIG. FIG. 4 is an exemplary screen display illustrating a third embodiment of an automatic SSEP execution screen that forms part of the neurophysiology system of FIG. 1. 2 is a screen shot of an example of a manual MEP monitoring screen that forms part of the neurophysiology system of FIG. 2 is a screen shot of an example of an automatic MEP monitoring screen that forms part of the neurophysiology system of FIG. 2 is a screen shot of an example of a twitch test monitoring screen that forms part of the neurophysiology system of FIG. 2 is a screen shot of an example of a basic stimulus EMG monitoring screen that forms part of the neurophysiology system of FIG. 2 is a screen shot of an example of a dynamic stimulus EMG monitoring screen that forms part of the neurophysiology system of FIG. 2 is a screen shot of an example of a neurological observation EMG monitoring screen that forms part of the neurophysiology system of FIG. 2 is a screen shot of an example of a continuous EMG monitoring screen that forms part of the neurophysiology system of FIG. 2 is a screen shot of an example of a navigation guidance screen that forms part of the neurophysiology system of FIG. FIG. 6 is a graph illustrating the basic steps of a fast current threshold search algorithm, according to one embodiment of the present invention. 4 is a graph illustrating the basic steps of a fast current threshold search algorithm, according to one embodiment of the present invention. 4 is a graph illustrating the basic steps of a fast current threshold search algorithm, according to one embodiment of the present invention. 4 is a graph illustrating the basic steps of a fast current threshold search algorithm, according to one embodiment of the present invention. FIG. 36 is a block diagram illustrating the starting order of steps for determining an associated safety level prior to determining an exact threshold, according to an alternative embodiment of the threshold search algorithm of FIGS. 6 is a flow chart illustrating a method by which a multi-channel search algorithm determines whether stimulation should be performed or omitted. FIG. 40 is a graph illustrating the use of the threshold search algorithm of FIG. 39 and further omitting stimuli when similar results are already apparent from previous data. FIG. 40 is a graph illustrating the use of the threshold search algorithm of FIG. 39 and further omitting stimuli when similar results are already apparent from previous data. FIG. 40 is a graph illustrating the use of the threshold search algorithm of FIG. 39 and further omitting stimuli when similar results are already apparent from previous data. FIG. 6 is a flow chart illustrating the order employed by the algorithm to determine and monitor I _thresh . FIG. FIG. 6 is a graph illustrating a confirmation step employed by an algorithm to determine whether I _thresh has changed from a previous determination. FIG. 6 is a flow chart showing the steps used to automatically determine the optimal parameters of SSEP peripheral nerve stimulation for all four limbs. FIG. 5 is a flow chart showing the steps used to automatically determine the optimal parameters of SSEP peripheral nerve stimulation for one limb utilizing a threshold determination algorithm.

  Illustrative embodiments of the invention are described below. For clarity, not all mechanisms actually implemented are described herein. Of course, in the development of any such actual embodiment, a number of realizations to achieve the specific purpose of the developer, such as compliance with system-related and business-related constraints, which vary from implementation to implementation. It is understood that a decision specific to this should be made. Further, it is understood that such development efforts can be complex and time consuming, yet can be routine for those skilled in the art having the benefit of this disclosure. The systems disclosed herein boast a variety of inventive features and components that ensure patent protection both individually and in combination. Also, the surgical systems and related methods described herein are generally described herein for use in spinal surgery, but assess the health of the spinal cord and / or various other neural tissues. It is also explicitly noted that it is suitable for any number of additional procedures, such as surgery or otherwise, that may prove to be beneficial.

  A surgeon-operable neurophysiology system 10 is described herein and performs numerous neurophysiological and / or guidance assessments at the direction of the surgeon (and / or other members of the surgical team). Can be implemented. By way of example only, FIGS. 1-2 illustrate the basic components of the neurophysiology system 10. The system includes a control unit 12 (preferably comprising a main display 34 with a graphical user interface (GUI) and a processing unit 36 collectively containing processing functions essential to control the system 10). , Patient module 14, stimulation aids (eg, stimulation probe 16, stimulation clip 18 for connection to various surgical instruments, in-line stimulation hub 20, and stimulation electrode 22), and a plurality for detecting potential. Recording electrode 24. Stimulation clip 18 includes any of a variety of surgical instruments including, but not necessarily limited to, pedicle access needle 26, k-line 27, tap 28, dilator (s) 30, tissue retractor 32, and the like. Can be used to connect to the system 10. One or more auxiliary feedback devices (eg, auxiliary display 46 of FIGS. 11-12) may also be provided for additional representations of output to the user and / or for receiving input from the user.

  In one embodiment, the neurophysiology system 10 includes a static carcass integrity test (“basic stimulation EMG”), a dynamic carcass integrity test (“dynamic stimulation EMG”), neural proximity detection (“XLIF® registration”). TM) "), neuromuscular pathway assessment (" Spasticity test "), motor evoked potential monitoring (" Manual MEP "and" Automatic MEP "), somatosensory evoked potential monitoring (" Manual SSEP "and" Automatic SSEP "), It can be configured to perform any functional mode, including but not necessarily limited to non-triggered monitoring (“persistent EMG”), as well as surgical navigation (“navigation guidance”). The neurophysiology system 10 can also be configured for implementation in any of the lumbar region, thoracolumbar region, and cervical region of the spine.

  Prior to focusing on the various functional modes of the surgical system 10, the hardware components and mechanisms of the system 10 will be described in more detail. By way of example only, the control unit 12 of the neurophysiology system 10 illustrated in FIG. 3 includes a main display 34 and a processing unit 36 that collectively contains the processing functions essential to control the neurophysiology system 10. including. The main display 34 preferably comprises a graphical user interface (GUI) that can communicate information graphically to the user and receive instructions from the user. The processing unit 36 commands the stimulation source (eg, the patient module 14, FIGS. 4-6), receives digital and / or analog signals and other information from the patient module 14, and processes the EMG and SSEP response signals. Contains computer hardware and software that displays processed data to the user via display 34. The main functions of the software in the control unit 12 include receiving user commands via the touch screen main display 34 and suitable modes (basic stimulation EMG, dynamic stimulation EMG, XLIF, automatic MEP, manual MEP, Enabling stimulation with manual SSEP, automatic SSEP, and spasm tests, processing signal data according to a defined algorithm, displaying received parameters and processed data, and monitoring system status including. According to an exemplary embodiment, the main display 34 may comprise a 15 inch LCD display with suitable touch screen technology and the processing unit 36 may comprise 2 GHz. The processing unit 36 shown in FIG. 3 includes a powered USB port 38 for connection to the patient module 14, a media drive 40 (eg, CD, CD-RW, DVD, DVD-RW, etc.), network A plurality of additional ports 42 (e.g., a port, wireless network card, and, by way of example, for attaching additional auxiliary devices such as navigation guidance sensors, co-stimulator anodes, external devices (e.g., printers, keyboards, mice, etc.) USB, IEEE 1394, infrared, etc.). Preferably, in use, the control unit 12 is located outside the surgical field, but near the surgical table, such as, for example, on a table or on a movable stand. However, it is understood that the control unit 12 can be placed in a surgical (sterile) field if properly covered and protected.

  By way of example only, the patient module 14 shown in FIGS. 4-6 is linked in communication with the control unit 12. In this embodiment, the patient module 14 is linked to communicate with the control unit 12 via the USB data cable 44 and receives power therefrom. However, providing the patient module 14 with its own power supply and other known data cables and wireless technologies that can be utilized to establish communication between the patient module 14 and the control unit 12 It is understood that The patient module 14 includes a digital communication interface for communicating with the control unit 12 and basic stimulation EMG, dynamic stimulation EMG, XLIF®, spasm test, manual MEP and automatic MEP, and SSEP, but not necessarily Electrical to all recording and stimulation electrodes, signal conditioning circuitry, stimulator drive and steering circuitry, and signal conditioning circuitry required to implement all functional modes of the neurophysiological system 10, including but not limited to Contains connections. In one example, the patient module 14 includes 32 recording channels and 11 stimulation channels. A display (eg, an LCD screen) can be provided on the surface of the patient module 14 and simple status readings (eg, power-up test results, attached electrode harness, and impedance data), or more Treatment related data (eg, stimulation threshold results, current stimulation level, selected function, etc.) can be utilized. The patient module 14 can be positioned near the patient in the sterile field during surgery. As an example, patient module 14 may be attached to the bed rail using hooks 48 attached to or forming part of the casing of patient module 14.

  4-6, the patient module 14 includes a number of ports and indicators for connecting between the patient module 14 and other system components and for verifying the connection. The control unit port 50 is provided for communicating data and power with the control unit 12 via the USB data cable 44 as described above. The four auxiliary ports 52 include a stimulation probe 16, a stimulation clip 18, an in-line stimulation hub 20, and a navigation guidance sensor (or tilt sensor) 54 for up to the same number of surgical operations, but not necessarily limited thereto. Provided to connect auxiliary equipment. Auxiliary port 52 includes a stimulation cathode and transmits digital communication signals, tri-color LED drive signals, button status signals, identification signals, and power between patient module 14 and attached auxiliary devices. If it is desirable or necessary to attach a co-stimulator anode during the procedure, preferably a pair of anode ports 56 with two linear DIN connectors can be used to do so. A pair of USB ports 58 are connected to the control unit 12 as USB hubs and can be used to create any number of connections, such as a portable storage drive, by way of example only.

  As soon as the device is plugged into any one of the ports 50, 52, 56, or 58, the neurophysiology system 10 checks the circuit to ensure that the associated device operates normally. Conduct continuity check automatically. Each device forms a separate closed circuit with the patient module so that the devices are identified independently of each other. If one device is not operating properly, the devices can be individually identified while the remaining devices continue to show their valid status. In order to convey the result of the continuity confirmation to the user, an indicator LED is provided for each port. Thus, according to one exemplary embodiment of FIGS. 7-9, patient module 14 includes one control unit indicator 60, four auxiliary indicators 62, two anode indicators 64, and two USB indicators 66. including. According to a preferred embodiment, if the system detects an incomplete circuit during the continuity check, the appropriate indicator turns red to alert the user that the device is not operating properly. On the other hand, if a complete circuit is detected, the indicator will show a green color to indicate that the device should operate as desired. Additional indicator LEDs can be provided to indicate system and MEP stimulus status. The system indicator 68 shows green when the system is operational and red when the system is not operational. The MEP stimulation indicator 70 is lit when the patient module is ready to deliver a MEP stimulation signal. In one embodiment, the MEP stimulus indicator 68 shows a yellow color to indicate the ready state.

  To connect the array of recording electrodes 24 and stimulation electrodes 22 utilized by the system 10, the patient module 14 also includes a plurality of electrode harness ports. In the illustrated embodiment, the patient module 14 includes an EMG / MEP harness port 72, an SSEP harness port 74, and an auxiliary harness port 76 (for expansion and / or custom harness). Each harness port 72, 74, and 76 includes a shaped socket 78 that corresponds to a matching shaped connector 82 on a suitable electrode harness 80. In addition, the neurophysiology system 10 can preferably employ a color code system where each modality (eg, EMG, EMG / MEP, and SSEP) has a unique color associated with it. By way of example only and as shown herein, EMG monitoring (including screw testing, detection, and nerve retractor) is associated with green, MEP monitoring is associated with blue, and SSEP monitoring is orange. It may be associated with a color. Accordingly, each harness port 72, 74, 76 is marked with a suitable color, which also corresponds to a suitable harness 80. Utilizing a combination of dedicated color code and shaped socket / connector interface simplifies system setup, reduces errors, and minimizes the amount of pre-operative preparation required. The configuration of the patient module 14 and, in particular, the various port and indicator numbers and arrangements have been described according to an exemplary embodiment of the present invention. However, it should be understood that the patient module 14 can be configured in any number of different arrangements without departing from the scope of the present invention.

  As described above, all recording electrodes 24 and stimulation electrodes 22 (within the patient module 14) required to implement one of various functional modes are provided to simplify the setup of the system 10. The pre-amplifier includes a common electrode 23 that provides a ground reference and an anode electrode 25 that provides a return path for the stimulation current), by way of example only, and is bundled together as illustrated in FIG. One electrode harness 80 is provided. Depending on the desired function (s) used during a particular procedure, different groupings of recording electrodes 24 and stimulation electrodes 22 may be required. As an example, the SSEP function requires more stimulation electrodes 22 than either the EMG function or the MEP function, but also requires fewer recording electrodes than either the EMG function or the MEP function. In order to take into account the different electrode requirements of the various functional modes, the neurophysiology system 10 can employ different harnesses 80 depending on the desired mode. According to one embodiment, three different electrode harnesses 80 for use with the system 10, EMG harness, EMG / MEP harness, and SSEP harness may be provided.

  One end of the harness 80 is a shaped connector 82. As described above, shaped connector 82 interfaces with shaped sockets 72, 74, or 76 (depending on the functionality provided for harness 80). Each harness 80 utilizes a shaped connector 82 that corresponds to a suitable shaped socket 72, 74, 76 on the patient module 14. If the socket and connector shapes do not match the harness 80, a connection with the patient module 14 cannot be established. According to one embodiment, the EMG and EMG / MEP harnesses are both plugged into the EMG / MEP harness port 72, so they both utilize the same shaped connector 82. By way of example only, FIGS. 8A-8C illustrate various shape profiles used by different harness ports 72, 74, 76 and connector 82. FIG. 8A illustrates a semi-circular shape associated with EMG and EMG / MEP harness and port 72. FIG. 8B illustrates the rectangular shape utilized by the SSEP harness and port 74. Finally, FIG. 8C illustrates the triangular shape utilized by the auxiliary harness and port 76. Each harness connector 82 includes a digital identification signal that identifies the type of harness 80 to the patient module 14. The opposite end of the electrode harness 80 is a plurality of electrode connectors 102 linked to the harness connector 82 via lead wires. Using the electrode connector 102, by way of example only, any of a variety of known electrodes such as surface dry gel electrodes, surface wet gel electrodes, and needle electrodes can be used.

  To facilitate simple placement of scalp electrodes used during MEP and SSEP modes, the electrode cap 81 depicted in FIG. 10A can be used by way of example only. The electrode cap 81 includes two recording electrodes 23 for SSEP monitoring, two stimulation electrodes 22 for MEP stimulation delivery, and an anode 23. A graphical indicator can be used on the electrode cap 81 to depict different electrodes. As an example, lightning bolts may be used to indicate stimulation electrodes, double circles may be used to indicate recording electrodes, and stepped arrows may be used to indicate anode electrodes. Good. The anode electrode line is colored white to further distinguish it from the other electrodes and is significantly longer than the other electrode lines so that the anode electrode can be placed on the patient's shoulder. Further, the shape of the electrode cap 81 can be designed to simplify the placement. By way of example only, the cap 81 has a point that can point directly in the direction of the patient's nose when the cap 81 is centered over the head in the correct orientation. A single wire can connect the electrode cap 81 to the patient module 14 or the electrode harness 80, thereby reducing the group of wires around the upper region of the patient. Alternatively, the cap 81 can comprise a power supply device and a wireless antenna for communicating with the system 10. FIG. 10B illustrates another exemplary embodiment of an electrode cap 83 that is similar to the cap 81. Rather than using graphical indicators to distinguish the electrodes, colored lines can be employed. As an example, the stimulation electrode 22 may be colored yellow, the recording electrode 24 may be colored gray, and the anode electrode 23 may be colored white. Here, the anode electrode appears to be configured for placement on the patient's forehead. According to alternative embodiments, an electrode cap (not shown) can comprise a strap or set of straps configured to be worn over the patient's head. A suitable scalp recording and stimulation site may be indicated on the strap. As an example, the electrode cap can have a hole on each of the scalp recording site (for SSEP) and the scalp stimulation site (for MEP). According to a further exemplary embodiment, the perimeter of each hole may be color coded to match the color of the electrode lead specified for that site. In this case, the recording and stimulation electrode designated for the scalp is preferably one of a needle electrode and a spiral electrode that can be placed on the scalp through a hole in the cap.

  In addition to or instead of color-coding the electrode leads for the intended intended placement, the end of each lead next to the electrode connector 102 indicates the proper positioning of the electrodes on the patient , Or represent, can be tagged with a label 86. The label 86 preferably specifies the proper electrode placement graphically and textually. As shown in FIG. 9, the label can include a graphical image showing the associated body part 88 and the exact electrode location 90. In the text, the label 86 indicates the flank 100 and muscle (or anatomical location) 96 for placement, electrode function (eg, stimulation, recording channel, anode, and reference—not shown), patient skin surface (eg, , Anterior or posterior), spinal cord region 94, and type of monitoring 92 (eg, EMG, MEP, SSEP, by way of example only). According to one embodiment (described by way of example only), the electrode harness 80 may have various electrodes, including: Lumbar EMG Table 1, Neck EMG Table 2, Lumbar / Chest Lumbar EMG and MEP Table 3 Designed to be positioned around the patient (and preferably labeled as appropriate), as described in Table 4, Cervical EMG and MEP, and Table 5 in SSEP.

上述されるように、神経生理学的監視システム１０は、ほんの一例として、図１１〜１２に図示される、補助ディスプレイ４６等の補助ディスプレイを含むことができる。補助ディスプレイ４６は、主ディスプレイ３４上に提供される情報のうちのいくつか、またはすべてを表示するように構成することができる。補助ディスプレイ３４上でユーザに表示される情報には、任意の選択された機能モード（例えば、手動ＳＳＥＰ、自動ＳＳＥＰ、手動ＭＥＰ、自動ＭＥＰ、攣縮試験、基礎刺激ＥＭＧ、動的刺激ＥＭＧ、ＸＬＩＦ、持続ＥＭＧ、およびナビゲーションガイダンス）、取り付けられた補助器（例えば、刺激プローブ１６、刺激クリップ１８、傾斜センサ５４）、取り付けられる電極ハーネス（単数または複数）、インピーダンス試験結果、筋節／ＥＭＧレベル、刺激レベル、履歴報告、選択されたパラメータ、試験結果等に関する、英数字および／または図式情報が挙げられるが、必ずしもこれらに限定されない。一実施形態では、補助ディスプレイ４６は、その表示機能に加えて、ユーザ入力を受信するように構成することができる。したがって、補助ディスプレイ４６は、システム１０の代替の制御点として使用することができる。制御ユニット１２および補助ディスプレイ４６は、他方のディスプレイに示される出力を変化させることなく、一方のディスプレイから入力が受信されるように、リンクすることができる。これは、依然として、ＯＲスタッフの他の構成員が、様々な目的（例えば、注釈を入力する、履歴を閲覧する等）のために、システム１０を操作することを可能にする一方で、執刀医が、患者および試験結果への集中を維持することを可能にし得る。補助ディスプレイ４６は、電池式であってもよい。有利に、補助ディスプレイ４６は、無菌野の中、ならびに無菌野の外に位置付けることができる。無菌野内に位置付けるために、ディスプレイを収容するための使い捨ての無菌ケース４７が提供されてもよい。代替として、ディスプレイ４６は、無菌バッグに入れることができる。無菌ケース４７および補助ディスプレイ４６の両方は、外科手術野の近くおよび／またはその中に見られる、ポール、ベッドフレーム、照明器具、あるいは他の装置に取り付けることができる。複数の補助ディスプレイ４６を制御ユニット１２にリンクすることができることがさらに熟考される。これは、神経生理学情報を効果的に分散し、手術室全体を制御し得る。一例として、また、麻酔医に補助ディスプレイ４６を提供することができる。これは、麻酔医に攣縮試験からの結果を提供し、神経生理学システム１０の精度に悪影響を及ぼし得る、麻痺薬の使用についての注意を提供するのに特に有用であり得る。補助ディスプレイ４６を制御ユニット１２にリンクするために、有線または無線技術が利用されてもよい。

As described above, the neurophysiological monitoring system 10 can include an auxiliary display, such as the auxiliary display 46 illustrated in FIGS. 11-12, by way of example only. Auxiliary display 46 may be configured to display some or all of the information provided on main display 34. Information displayed to the user on the auxiliary display 34 includes any selected functional mode (eg, manual SSEP, automatic SSEP, manual MEP, automatic MEP, spasm test, basal stimulation EMG, dynamic stimulation EMG, XLIF, Persistent EMG and navigation guidance), attached auxiliary devices (eg, stimulation probe 16, stimulation clip 18, tilt sensor 54), attached electrode harness (s), impedance test results, sarcomere / EMG level, stimulation Examples include, but are not necessarily limited to alphanumeric and / or graphical information regarding levels, historical reports, selected parameters, test results, etc. In one embodiment, auxiliary display 46 may be configured to receive user input in addition to its display capabilities. Thus, the auxiliary display 46 can be used as an alternative control point for the system 10. The control unit 12 and the auxiliary display 46 can be linked such that input is received from one display without changing the output shown on the other display. This still allows other members of the OR staff to operate the system 10 for various purposes (eg, entering annotations, browsing history, etc.), while the surgeon. May be able to maintain focus on the patient and test results. The auxiliary display 46 may be battery powered. Advantageously, the auxiliary display 46 can be positioned in the sterile field as well as outside the sterile field. A disposable aseptic case 47 for housing the display may be provided for positioning in the sterile field. Alternatively, the display 46 can be placed in a sterile bag. Both sterile case 47 and auxiliary display 46 can be attached to a pole, bed frame, luminaire, or other device found near and / or within the surgical field. It is further contemplated that multiple auxiliary displays 46 can be linked to the control unit 12. This can effectively distribute neurophysiological information and control the entire operating room. As an example, an anesthesiologist can also be provided with an auxiliary display 46. This can be particularly useful to provide anesthesiologists with the results from the spasm test and to give attention to the use of paralytic drugs that can adversely affect the accuracy of the neurophysiological system 10. Wired or wireless technology may be utilized to link the auxiliary display 46 to the control unit 12.

  Having described exemplary embodiments of the system 10 and the hardware components comprising it, the neurophysiological functionality and methodology of the system 10 will now be described in more detail. Various parameters and configurations of the nerve monitoring system 10 may depend on the target location of the surgical procedure (ie, spinal cord region) and / or user preferences. In one embodiment, when the system 10 is activated, the software opens an activation screen, illustrated in FIG. 13 by way of example only. The startup screen allows the user to select one of the standard profiles or any custom profile previously saved in the system (eg, “Standard Neck”, “Standard Chest / Lumbar”, and “Standard Lumbar”) A profile selection window 160 is included. The profiles can be arranged in alphabetical order, in the spinal cord region, or other suitable criteria for selection. The profile can be stored on the hard drive of the control unit or on a portable memory device such as a USB memory drive or on a web server.

  By selecting a profile, the system 10 is configured with parameters assigned to the selected profile (standard or custom). The availability of different functional modes may depend on the profile selected. By way of example only, the selection of the cervical and thoracolumbar spinal cord regions selects manual SSEP, automatic SSEP, manual MEP, automatic MEP, spasm test, basal stimulation EMG, dynamic stimulation EMG, XLIF, continuous EMG, and navigation guidance mode Choices can be configured automatically, while lumbar region selection selects spasm, basic, differential, and dynamic stimulation EMG tests, XLIF®, and neural retractor mode Choices can be automatically configured as possible. Also, the initial parameters associated with the various functional modes may depend on the selected profile, for example, the characteristics of the stimulation signal delivered by the system 10 may vary from profile to profile. As an example, the stimulation signal utilized for the stimulation EMG mode can be configured to be different when a lumbar profile is selected as compared to when one of a thoracolumbar profile and a cervical profile is selected. .

  As described above, each of the hardware components includes an identification tag that allows the control unit 12 to determine which devices are connected and ready for surgery. In one embodiment, the profile can also be selected only if a suitable device (eg, an appropriate electrode harness 80 and stimulation aid) is connected and / or ready for surgery. Alternatively, the software can jump directly to one of the functional modes, jumping over the activation screen, based on the fact that it has a known auxiliary and / or harness plugged. The ability to select a profile based on standard parameters, and particularly customized preferences, can save significant time when a procedure is undertaken, providing monitoring availability immediately after initiation. Moving from the startup screen, the software proceeds directly to the electrode test screen and impedance test performed on every electrode as described above. When the acceptable impedance test is complete, the system 10 is ready to begin monitoring and the software proceeds to a monitoring screen where the neurophysiological monitoring functions of the system 10 are performed.

  Information displayed on the monitoring screen includes any functional mode (eg, manual SSEP, automatic SSEP, manual MEP, automatic MEP, spasm test, basal stimulation EMG, dynamic stimulation EMG, XLIF, sustained EMG, and navigation guidance). ), Attached auxiliary devices (eg stimulation probe 16, stimulation clip 18, tilt sensor 54), attached electrode harness (s), impedance test results, sarcomere / EMG level, stimulation level, history report, selection Include, but are not necessarily limited to, alphanumeric and / or graphical information relating to the measured parameters, test results, etc. In one embodiment described by way of example only, this information displayed on the main monitoring screen includes, but is not necessarily limited to, the following components described in Table 6.

ほんの一例として、図１４に図示される、プロファイル設定ウィンドウ１６０から、カスタムプロファイルを作成し、保存することができる。標準プロファイルのうちの１つで開始して、音声１６８、部位選択１７０、試験選択１７２、および波形拡大縮小１７４ボタンのうちの１つを選択し、所望のパラメータが設定されるまで変更を行うことによって、パラメータを変えることができる。ほんの一例として、プロファイルは、特定の処置（例えば、ＡＣＤＦ、ＸＬＩＦ、および減圧）、特定の個人、およびその組み合わせのために生成し、保存することができる。各ボタンをクリックすることで、選択されるボタンに特異なパラメータ選択肢が、パラメータウィンドウ１７６内に表示される。試験選択ウィンドウのパラメータ選択肢は、一例として、図１４に図示される。ほんの一例として、試験選択ボタンを選択することによって、セッション試験を追加し、表示選択肢を変更することができる。試験選択域内から、すべての使用可能な試験機能（部位選択、使用可能なデバイス等に基づく）の機能に特異なパラメータがアクセスされ、要求に従って設定され得る。試験選択ボタンの下で複数の機能に使用可能な一選択肢は、３つの異なる表示選択肢から選択する能力である。ユーザは、数値形式で表示される結果、身体パネル上に表示される結果、および各電極に関連付けられるラベルを反映するラベル上に反映される結果、またはこの３つの任意の組み合わせを見ることを選択することができる。また、ユーザは、実際の波形を見ることを選択することができる。波形拡大縮小ボタン１７４を選択することによって、ユーザは、波形が表示される縮尺を調節することができる。音声ボタン１６８を選択することによって、システム音声および持続音声の両方を調節することができる。部位選択ボタン１７０を選択することによって、初期に選択された部位から変更する機会が設けられる。プロファイルの部位選択を調節することによって、使用可能な選択肢を変えることができる。一例として、ユーザが部位選択を頸部から腰部に変更する場合、ＭＥＰ機能は、もはや選択肢として選択可能ではない場合がある。図１３は、部位選択画面の実施例である。図１９〜２６、２８〜３５は、試験機能（例えば、手動ＳＳＥＰ、自動ＳＳＥＰ、手動ＭＥＰ、自動ＭＥＰ、攣縮試験、基礎刺激ＥＭＧ、動的刺激ＥＭＧ、ＸＬＩＦ、持続ＥＭＧ、およびナビゲーションガイダンス）のそれぞれの試験選択タブの実施例を図示する。プロファイルは、制御ユニット１２上に直接保存することができ、もしくはそれらは、携帯型メモリデバイスに保存することができ、またはウェブサーバ上にアップロードすることができる。

By way of example only, a custom profile can be created and saved from the profile settings window 160 illustrated in FIG. Start with one of the standard profiles and select one of the voice 168, site selection 170, test selection 172, and waveform zoom 174 buttons and make changes until the desired parameters are set Can change the parameters. By way of example only, profiles can be generated and stored for specific treatments (eg, ACDF, XLIF, and reduced pressure), specific individuals, and combinations thereof. By clicking each button, parameter options specific to the selected button are displayed in the parameter window 176. The parameter selections in the test selection window are illustrated in FIG. 14 as an example. By way of example only, a session test can be added and the display options can be changed by selecting the test selection button. From within the test selection area, parameters specific to the functions of all available test functions (based on site selection, available devices, etc.) can be accessed and set according to requirements. One option available for multiple functions under the test selection button is the ability to select from three different display options. The user chooses to see the results displayed in numeric form, the results displayed on the body panel, and the results reflected on the labels that reflect the labels associated with each electrode, or any combination of the three can do. The user can also choose to see the actual waveform. By selecting the waveform enlargement / reduction button 174, the user can adjust the scale at which the waveform is displayed. By selecting the audio button 168, both system audio and sustained audio can be adjusted. By selecting the region selection button 170, an opportunity to change from the initially selected region is provided. By adjusting the site selection of the profile, the available options can be changed. As an example, if the user changes the site selection from neck to waist, the MEP function may no longer be an option. FIG. 13 is an example of the part selection screen. 19-26, 28-35 show test functions (eg, manual SSEP, automatic SSEP, manual MEP, automatic MEP, spasm test, basal stimulation EMG, dynamic stimulation EMG, XLIF, sustained EMG, and navigation guidance), respectively. FIG. 6 illustrates an example of a test selection tab of FIG. The profiles can be stored directly on the control unit 12, or they can be stored on a portable memory device or uploaded on a web server.

  Here, various mechanisms of the GUI monitoring screen 200 will be described. The patient module 14 is configured so that once the system is set up, the electrode harness is connected and applied to the patient, the neurophysiology system 10 can perform impedance tests under the direction of the control unit 12 of all electrodes. Is done. Upon activation of the program, the user is automatically directed to an electrode test after selecting a suitable spinal cord site (described below). FIG. 16 illustrates, by way of example only, an electrode test mechanism with a schematic implementation of an electrode test screen, according to an exemplary embodiment of a GUI. The electrode test screen 104 includes a human figure 105 with an electrode position indicator 108. The harness indicator 109 displays the harness (s) 80 connected to the patient module 14. There is a corresponding channel button 110 on each electrode on the harness (es) 80 in use, including the common electrode 25 and the anode electrode 23. Preferably, the common electrode 25 and the anode electrode 23 are independently checked for acceptable impedance. To accomplish this, both the anode electrode 23 and the common electrode 25 are provided as double electrodes. At least one of the anode leads on the anode electrode is reversible. During impedance verification, the reversible anode lead is switched to the cathode so that the impedance between the leads can be measured. When the impedance test is complete, the reversible lead switches back to the anode. The channel button 110 can be labeled with the muscle name or the area of interest of the corresponding electrode. Stimulation electrodes can be indicated by symbols such as lightning or other indicators, by way of example only, to distinguish between recording electrodes and stimulation electrodes. By selecting the channel button 110, the associated channel is disabled. Disabled channels are not tested for impedance unless they are re-enabled (eg, by selecting the corresponding channel button 110 again) and they are not monitored for responses or errors. Upon selecting the start button 106 (named “Execute Electrode Test”), the system 10 tests each electrode individually to determine the impedance value. If the impedance is determined to be within acceptable limits, the channel button 110 and corresponding electrode depiction on the human figure 108 will be green. If the impedance value of any electrode is not determined to be acceptable, the associated channel button 110 and electrode depiction will turn red, alerting the user. Once the test is complete, selecting the approval button 112 opens the main monitoring screen of the system 10.

  The functions performed by the neuromonitoring system 10 include the spasm test, sustained EMG, basal stimulation EMG, dynamic stimulation EMG, XLIF®, nerve retractor, manual MEP, automatic MEP, which are briefly described below. And manual SSEP, automatic SSEP, and navigation guidance mode. The spasm test mode ensures that there are no muscle relaxants in the neuromuscular pathway prior to performing neurophysiology based tests such as bone integrity (e.g., carcass) testing, nerve detection, and nerve incision wounds, It is designed to assess neuromuscular pathways via the so-called “quadruple test”. This is under the name “System and Methods for Assessing the Neuropathic Pathway Prior to Nerve Testing”, filed on October 7, 2005, and more fully described in PCT Patent Application No. PCT / US2005 / 036089. The contents of are hereby incorporated by reference as if fully set forth herein. The basic stimulus EMG and dynamic stimulus EMG tests are performed during all aspects of pilot hole formation (eg, via awl), pilot hole preparation (eg, via a tap), and screw introduction (middle and later). Designed to assess bone integrity (eg, carcass). These modes are named “System and Methods for Performing Percutaneous Pedicle Integrity Assessments”, PCT patent application No. PCT / US02 / 35047, filed on October 30, 2002, and named “System ford medm “Pedicle Integrity Assets”, described in more detail in PCT Patent Application No. PCT / US2004 / 025550, filed on August 5, 2004, the entire contents of which are both incorporated herein by reference. Which is incorporated herein by reference as if fully set forth herein. The XLIF mode is designed to detect the presence of nerves during use of various surgical access instruments of the nerve monitoring system 10, including the pedicle access needle 26, k-line 42, dilator 44, retractor assembly 70. Is done. This mode has the name “System and Methods for Determining Nerve Proximity, Direction, and Pathology Duty Surgency” and is described in detail in PCT Patent Application No. PCT / US2002 / 22247 filed on July 11, 2002. The entire contents of which are hereby incorporated by reference as if fully set forth herein. The nerve retractor mode is designed to assess nerve health or pathology before, during, and after a nerve incision during a surgical procedure. This mode is described in more detail in PCT Patent Application No. PCT / US2002 / 30617, filed on September 25, 2002, under the name “System and Methods for Performing Surgical Procedures and Assessments”. Are hereby incorporated by reference as if fully set forth herein. Automatic and manual MEP modes test for motor pathways, stimulate the motor cortex in the brain, and record potential EMG responses as a result of various muscles in the upper and lower limbs, thereby reducing potential damage to the spinal cord. Designed to detect. The SSEP function is designed to detect potential damage to the spinal cord by examining sensory pathways, stimulating peripheral nerves below the target spinal cord level, and recording action potentials from sensors above the spinal cord level. Designed. Auto MEP, Manual MEP, and SSEP modes are named PCT Patent Application No. PC66 / US66 / US66 / US Patent Application No. PC66 / 200, filed on Feb. 2, 2006 under the name “System and Methods for Performing Neurophysical Assessments, During Spine Surgery”. The entire contents of which are described and incorporated herein by reference as if fully set forth herein. The navigation guidance function provides the ability to determine the optimal or desired trajectory of a surgical instrument and / or graft and provide the ability to monitor the trajectory of the surgical instrument and / or graft during surgery. Designed to facilitate safe and reproducible use of surgical instruments and / or implants. This mode is named “Surgical Trajectory Monitoring System and Related Methods”, filed on July 30, 2007, in PCT Patent Application No. PCT / US2007 / 11962 and PCT Patent Application No. PCT / US2008 / 12121. Each of which is hereby incorporated by reference in its entirety as if fully set forth herein. These functions will now be briefly described in detail.

  The nerve monitoring system 10 performs an assessment of spinal cord health using one or more of automatic MEP, manual MEP, automatic SSEP, and manual SSEP modes.

  In SSEP mode, the nerve monitoring system 10 stimulates peripheral sensory nerves that exit the spinal cord below the level of surgery, and then generates an electrical action potential from electrodes placed on the nervous system above the surgical target site. taking measurement. Also applied to ensure that differences from normal or expected results are not due to stimulation signal delivery issues (eg, mispositioned stimulation electrodes, improper stimulation signal parameters, etc.) Recording sites below possible target sites are also preferably monitored as positive control measurements. To accomplish this, the stimulation electrode 22 may be placed on the skin over the desired peripheral nerve (such as the left and right posterior tibial nerve and / or the left and right ulnar nerve as examples only) and recorded. Electrodes 24 are positioned on the recording site (C2 vertebrae, Cp3 scalp, Cp4 scalp, elbow point, popliteal, etc. by way of example only) and stimulation signals are delivered from the patient module 14.

  Injury in the spinal cord interferes with the transmission of signals up the spinal thalamic pathway through the spinal cord, resulting in a debilitated signal, delayed at the recording site (eg, cortex and subcortical site) above the surgical location May result in signal or absence of signal. In order to confirm these occurrences, the system 10 monitors the amplitude and latency of the induced signal response. According to one embodiment, the system 10 can implement SSEP in one of two modes: automatic mode and manual mode. In automatic SSEP mode, the system 10 compares the difference between the amplitude and delay time of the signal response and the amplitude and delay time of the reference signal response. The difference is compared against pre-determined “safe” and “dangerous” levels and the result is displayed on display 34. According to one embodiment, the system can determine safety and risk levels for each stimulation channel individually based on the respective amplitudes and delay time values of cortical and subcortical sites. That is, if either the subcortical amplitude or cortical amplitude decreases by a predetermined level, or if either the subcortical delay time value or cortical delay time value increases by a predetermined level, the system alerts Can be issued. As an example, the alert may comprise a red, yellow, green alert associated with an applicable channel, where red indicates that at least one of the determined values is within a danger level; Green may indicate that all values are within the safety level, and yellow may indicate that at least one of the values is between the safety level and the danger level. In order to generate more information, the system 10 can analyze the combined results. In addition to the red, yellow, and green alarms, this information can be used by the system 10 to indicate possible causes of the results that are achieved. In manual SSEP mode, the signal response waveforms and the amplitude and delay time values associated with these waveforms are displayed to the user. The user can then make a comparison between the reference signal responses.

  17-22 are exemplary screen displays in “manual SSEP” mode, according to one embodiment of the nerve monitoring system 10. FIG. 17 illustrates an intraoperative monitoring (IOM) settings screen from which various mechanisms and parameters of manual SSEP mode can be controlled and / or adjusted as desired by the user. By using this screen, the user switches between manual mode and automatic mode, selects the stimulation speed, and selects each stimulation target site (eg, left ulnar nerve, right ulnar nerve, left tibial nerve, and right tibia). Have the opportunity to change one or more stimulation settings (eg, stimulation current, pulse width, and polarity). By way of example only, the user can first change one or more stimulation settings for each peripheral nerve by selecting one of the stimulation site tabs 264.

  Selecting one of the stimulation site tabs 264 opens a control window 265, seen in FIG. 18, from which various parameters of the manual SSPE test can be adjusted according to user preferences. By way of example only, FIG. 18 is an illustration of an on-screen display of a manual SSEP test setup for the left ulnar nerve stimulation site. The highlighted “left ulnar nerve” stimulation site tab 264 and pop-up window title 266 indicate that adjusting any setting changes the stimulation signal delivered to the left ulnar nerve. A plurality of adjustment buttons are used to set the parameters of the stimulus signal. According to one embodiment, the stimulation rate is selected from a range of 2.2 to 6.2 Hz, and the initial value may be 4.7 Hz. The amplitude setting can be increased or decreased in 10 mA increments using amplitude selection buttons 270 labeled (+10) and (−10) (by way of example only). By way of example only, amplitude selection buttons 272 labeled “+1” and “−1” can be used to make a more precise amplitude selection by increasing or decreasing the amplitude in 1 mA increments. . According to one embodiment, the amplitude is selected from the range of 1-100 mA, and the initial value may be 10 mA. The selected amplitude setting is displayed in box 274. The pulse width setting can be increased or decreased in 50 microsecond increments using width selection buttons 276 labeled “+50” and “−50”. According to one embodiment, the pulse width is selected from the range of 50-300 μsec, and the initial value may be 200 μsec. The exact pulse width setting 278 is shown in box 278. A polarity control 280 can be used to set the desired polarity of the stimulus signal. By pressing the SSEP stimulus start button 284 labeled “Start Stimulation” (by way of example only), SSEP stimulation with the selected stimulus settings can be initiated. Although stimulation setting adjustments are described with respect to the left ulnar nerve, it is understood that stimulation adjustments can be applied to other stimulation sites including, but not limited to, the right ulnar nerve and the left and right tibial nerves. . Alternatively, as described below, the system 10 can utilize an automatic selection process to quickly determine optimal stimulation parameters for each stimulation channel.

  In order to monitor the health of the spinal cord using SSEP, the user must be able to determine whether the response to the stimulus signal is changing. In order to monitor this change, a criterion is preferably determined during setup. This can be accomplished simply by selecting the “Set as Reference” button 298 next to the “Start Stimulation” button 284 on the settings screen illustrated in FIG. Having a determined baseline record for each stimulation site, subsequent monitoring can be performed as desired to obtain updated amplitude and delay time measurements throughout the treatment and recovery period.

  FIG. 19 depicts an exemplary screen display of the manual mode of the SSEP monitoring function. The mode indicator tab 290 on the test menu 204 indicates that “Manual SSEP” is the selected mode. The central result area 201 is divided into four sub-areas or channel windows 294, each dedicated to displaying the signal response waveform of one of the stimulating nerve sites. The channel window 294 depicts information including the neural stimulation site 295 and the waveform waterfall of each of the recording locations 291-293. For each stimulated neural site, the system 10 displays three signal response waveforms that represent measurements made at three different recording sites. By way of example only, for example, as shown in Table 5 above, the three recording sites are the peripheral 291 (from the peripheral nerve close to the stimulating nerve), the subcortical 292 (spine), and the cortex 293 (scalp). is there. Each zone may be associated with a graphical icon that illustrates the neural / skeletal structure. Although SSEP stimulation and recording have been described with respect to the neural stimulation sites and recording sites described above, SSEP stimulation can be located anywhere along the nervous system above the spinal cord level that is at risk during the procedure. It will be appreciated that it can be applied to any number of peripheral sensory nerves and recording sites.

  During SSEP mode (automatic and manual), a single waveform response is generated for each stimulus signal run (to each stimulus channel). The waveform is arranged using a stimulus at the extreme left and increasing time to the right. As an example, the waveform is captured within a 100 ms window following the stimulus. The stimulation signal execution consists of a predetermined number of stimulation pulses that fire at a selected stimulation frequency. By way of example only, the stimulation signal may include 300 pulses at a frequency of 4.7 Hz. A 100 ms window of data is acquired in each of the three SSEP recording channels, cortex, subcortex, and periphery. In order to eliminate asynchronous events so that only a synchronized evoked response remains after a sufficient number of pulses, for each sequential stimulus to the same channel during the stimulation, the three acquired waveforms are identical. Summed and averaged with previous waveforms during stimulation. Thus, the final waveform displayed by system 10 represents the average of the entire series (eg, 300) of detected responses.

  For each subsequent stimulus run, the waveform is depicted slightly downward each time until a total of four waveforms are shown, as depicted in FIGS. After 5 or more stimulus runs, the reference waveform is retained in addition to the waveforms from the previous 4 stimulus runs. Older waveforms are deleted from the waveform display. According to one embodiment, different colors can be used to represent different waveforms. For example, the reference waveform may be colored purple, the last stimulus run may be colored white, the penultimate stimulus run may be colored medium gray, and the remaining stimulus runs The earliest stimulus execution may be colored dark gray.

  According to one embodiment, markers 314, 316 can be placed on the reference and current waveforms that indicate the delay time and amplitude values associated with the waveform. The delay time is defined as the time from the stimulus to the first (earliest) marker. There is one “N” 314 and one “P” 316 marker in each waveform. The N marker is defined as the maximum average sample value within the window, and the P value is defined as the minimum average sample value within the window. The marker can comprise an intersection consisting of horizontal and vertical lines of the same color as the waveform. A text label 317 indicating the value at the marker is associated with each marker. The former of the two markers is labeled as a delay time (eg 22.3 ms). The latter of the two markers is labeled with an amplitude (eg, 4.2 μV). Amplitude is defined as the difference in microvolts between the average sample values at the marker. The delay time is defined as the time from the stimulus to the first (earliest) marker. Preferably, the markers are automatically placed by the system 10 (in both automatic and manual modes). In manual mode, the user can choose to place (and / or move) the marker manually.

  By further selecting one of the channel windows 294, the waveform contained within that window 294 is magnified. FIG. 22 is an exemplary illustration of an enlarged view achieved by selecting one of the channel windows 294. The enlarged view includes waveforms 291 to 293, a reference waveform, markers 314 and 316, control for moving marker 318, and waveform enlargement / reduction 332. Only the latest waveform is shown. The “Set All as Reference” button 310 allows the user to set (or change) all three recorded waveforms as references. Further, the criteria can be set (or changed) individually by pressing the individual “Set as Reference” button 312. In addition, the user can also move the N marker 314 and the P marker 316 as desired to establish a new measurement point. Direction control arrows 318 can be selected to move the N and P markers to the desired new position. Alternatively, the user can touch and drag the markers 314, 316 to a new location. By using the waveform control 332, the user can enlarge and reduce the recorded waveform.

  Referring to FIGS. 23-26, the automatic SSEP mode functions similarly to the manual SSEP mode, except that the system 10 determines the amplitude and delay time values and alerts the user if the values deviate. FIG. 23 shows an exemplary setting screen for automatic SSEP mode, by way of example only. Similar to the setting screen described above in the manual SSEP mode, the user can switch between manual mode and automatic mode, select the stimulation speed, and change one or more stimulation settings. By way of example only, the user first changes one or more stimulation settings for each peripheral nerve by selecting one of the stimulation site tabs 264, as described above with respect to manual mode and FIG. be able to. According to one embodiment, the stimulation rate is selected from the range of 2.2 to 6.2 Hz, the initial value may be 4.7 Hz, the amplitude is selected from the range of 1 to 100 mA, and the initial value is The pulse width may be selected from the range of 50 to 300 μsec, and the initial value may be 200 μsec.

  In automatic mode, the surgical system 10 also includes a timer function that can be controlled from the settings screen. Using the timer drop-down menu 326, the user can set and / or change the time interval for timer application. Two separate choices for the timer function, (1) (by way of example only) automatic stimulation on timeout, which can be selected by pressing the automatic start button 322, labeled “stimulus automatic start on timeout”, And (2) (by way of example only) there is a stimulus prompt promotion on timeout that can be selected by pressing the stimulus promotion button 324 labeled “Stimulation promotion on timeout”. After each SSEP monitoring episode, the system 10 starts a timer corresponding to the selected time interval, and when the time has elapsed, the system automatically performs the SSEP stimulation, or the stimulation, depending on the option selected. The reminder is activated. Stimulation prompts are, by way of example only, audible sounds, audio recordings, screen flashes, pop-up windows, scrolling messages, or combinations thereof, or to prompt the user to test SSEP again. Any other such alarm may be mentioned. It is also contemplated that the timer function described can be implemented in manual SSEP mode.

  24-26 depict exemplary on-screen displays of the automatic mode of the SSEP function. According to one embodiment, the user can choose to view a screen with only alphanumeric information (FIG. 25) and a screen with alphanumeric information and a recorded waveform (FIG. 24). The mode indicator tab 290 indicates that “Auto SSEP” is selected. The waveform selection tab 330 allows the user to select whether to display the waveform with alphanumeric results. Similar to the on-screen display described above in manual SSEP mode, the system 10 includes a channel window 294 for each neural stimulation site. Channel window 294 includes neural stimulation site 295, waveform recording, and associated recording locations 291-293 (peripheral, subcortical, and cortex), as well as the rate of change between reference and amplitude measurements, and reference and delay time measurements. Information including the rate of change between and can be displayed. By way of example only, each channel window 294 can optionally show a reference waveform and a current waveform for each recording site. In the event that the system 10 detects a significant decrease in amplitude or a significant increase in delay time, the relevant window is preferably displayed in a predetermined color (eg, red) to indicate to the surgeon the potential danger. Can be highlighted. Preferably, the stimulus result is sent to the surgeon along with the color code so that the user can easily grasp the risk and take corrective action to avoid or mitigate such risk. Is displayed. This can, for example, make it easier to allow SSEP monitoring results to be interpreted by a surgeon or assistant without requiring specialized neuromonitoring personnel. By way of example only, red is used when the decrease in amplitude or increase in delay time is within a predetermined risk level. Green indicates that the measured increase or decrease is within a predetermined safe level. Yellow is used for measurements that are between a predefined danger level and a safety level. By way of example only, system 10 may also notify the user of potential dangers through the use of warning message 334. The alert message is in the form of a pop-up window, but the alert is an audible sound, audio recording, screen flash, scrolling message, or any other such alert that informs the user of the potential danger. It is understood that the user can be communicated by one, or a combination thereof.

  Referring to FIG. 26, a pre-stimulation run can be selected at any time during the procedure for reconsideration. This can be accomplished, for example, by opening the event bar 208 and selecting the desired event. Details from the event are shown, history details are shown on the right side of the menu screen 302, and waveforms are shown in the central results screen. Again, the user can choose to reset the criteria for one or more nerve stimulation sites by pressing the appropriate “Set as Reference” button 306. In the example shown, the system 10 illustrates the waveform history at the 07:51 mark shown on the right side of the menu screen 302. The previous waveform history is saved by the surgical system 10 and stored in the waveform history toolbar 304. Although described only with respect to the automatic SSEP function, the same mechanism can be accessed from the manual SSEP mode, where the user presses the “Set as Reference” button 306 to record the recorded stimulation measurements for each neural stimulation. It is understood that one can choose to set as a site reference. By way of example only, the system 10 uses a “current criteria” notification 308 to notify the user whether an applicable event is already the current criteria.

  In addition to alerting the user of any change in the amplitude and / or delay time of the SSEP signal response, the neuromonitoring system 10 can detect from all recording sites to elucidate possible causes of the change in the SSEP response. It is further contemplated that the data can be evaluated. Based on that information, the program can suggest potential reasons for change. In addition, potential actions taken to avoid danger can be suggested. It is further contemplated that the neurophysiology system 10 can be linked to communicate with other devices in the operating room, such as, for example, anesthesia monitoring devices. Data from this other device can be considered by the program to provide higher accuracy and / or better suggestions. By way of example only, Table 7 illustrates that SSEPs illustrate various warnings that can be associated with specific SSEP results and combinations of results and are shown to the user. For example, in response to stimulation of the left ulnar nerve, the peripheral response from the elb point does not show a change in amplitude or delay time, the subcortical response shows a decrease in amplitude, and the cortical response shows a decrease in amplitude , The event box 206 (shown in FIG. 25) shows either a yellow or red indicator, as well as the text “Possible mechanical damage. Possible spinal cord ischemia.” As another example, if there is a decrease in amplitude or absence of response at all peripheral, subcortical, and cortical recording sites, the system can provide a “confirm electrode” warning 332 (FIG. 26). Depending on the current situation and the particular situation that results, such as the surgical procedure that resulted in the warning, the user may be better equipped to determine the most sensible sequence of actions.

上述されるように、システム１０は、各有効な刺激チャネル上でＳＳＥＰ試験を行うための最適刺激パラメータを素早く選択するために、自動化試験を採用することができる。これは、最も望ましい結果をもたらす組み合わせが達成されるまで、様々なパラメータを自動的に調節する、任意の数のアルゴリズムに従って行うことができる。一例として、システム１０は、ＥＭＧおよびＭＥＰモダリティのＩ_{ｔｈｒｅｓｈ}を発見するために、以下に記載される探索アルゴリズムと同様のアルゴリズムを利用することができる。本実施例によると、所望の刺激パラメータは、最初に、各刺激部位（例えば、左後脛骨神経（ＬＰＴＮ）、右後脛骨神経（ＲＰＴＮ）、左尺骨神経（ＬＵＮ）、および右尺骨神経（ＲＵＮ））の最低Ｉ_{ｔｈｒｅｓｈ}（既定の振幅Ｖ_{ｔｈｒｅｓｈ}を有する波形をもたらす、最低刺激信号強度である）を発見することによって判定される。ほんの一例として、ＬＰＴＮのＩ_{ｔｈｒｅｓｈ}を判定するために、極性Ａ（外科手術部位に近接するカソード）を使用して、初期の既定の刺激強度が、左ＰＴＮ刺激部位に経皮的に適用される。左膝窩の記録電極から、Ｖ_{ｔｈｒｅｓｈ}以上のＶ_ｐｐを伴う応答が取得されない場合、極性Ｂ（外科手術部位に近接するアノード）が使用され、同一の刺激強度が適用される。いずれの極性の第１の刺激レベルでも応答が取得されない場合、極性は、再度切り替えられ、刺激強度が２倍にされる。したがって、極性Ａを使用して、第２の刺激強度が適用される。左膝窩から応答が記録されない場合、極性は、反転され、同一の第２の強度の刺激が適用される。動員する（Ｖ_{ｔｈｒｅｓｈ}でのまたはそれを超えるＶ_ｐｐをもたらす）応答が依然として存在しない場合、刺激強度は、Ｖ_{ｔｈｒｅｓｈ}以上のＶ_ｐｐを伴う誘発電位が存在するまで、再度２倍にされる。左膝窩において、Ｖ_{ｔｈｒｅｓｈ}を達成する第１の誘発電位が記録される極性設定は、この刺激部位の極性として設定される。Ｖ_{ｔｈｒｅｓｈ}を達成する第１の刺激強度および直前の刺激強度は、初期区分（ｂｒａｃｋｅｔ）を形成する。

As described above, the system 10 can employ automated testing to quickly select the optimal stimulation parameters for performing SSEP testing on each available stimulation channel. This can be done according to any number of algorithms that automatically adjust the various parameters until the combination that yields the most desirable results is achieved. As an example, the system 10 can utilize an algorithm similar to the search algorithm described below to discover I _thresh for EMG and MEP modalities. According to this example, the desired stimulation parameters are initially determined for each stimulation site (eg, left posterior tibial nerve (LPTN), right posterior tibial nerve (RPTN), left ulnar nerve (LUN), and right ulnar nerve (RUN)). )) Minimum I _thresh (which is the minimum stimulus signal strength that results in a waveform with a predetermined amplitude V _thresh ). By way of example only, an initial predefined stimulation intensity is applied percutaneously to the left PTN stimulation site using polarity A (the cathode close to the surgical site) to determine the LP thr I _thresh. . If a response with a V _pp greater than or equal to V _thresh is not obtained from the left popliteal recording electrode, polarity B (anode close to the surgical site) is used and the same stimulation intensity is applied. If no response is obtained at the first stimulus level of any polarity, the polarity is switched again and the stimulus intensity is doubled. Accordingly, the second stimulus intensity is applied using polarity A. If no response is recorded from the left popliteal, the polarity is reversed and the same second intensity stimulus is applied. If there is still no response to mobilize (resulting in V _pp at or above V _thresh ), the stimulus intensity is doubled again until there is an evoked potential with V _pp greater than or equal to V _thresh . In the left poplite, the polarity setting at which the first evoked potential to achieve V _thresh is recorded is set as the polarity of this stimulation site. The first stimulus intensity that achieves V _thresh and the immediately preceding stimulus intensity form an initial bracket.

After the threshold current I _thresh is segmented, the initial segment is sequentially reduced to a predetermined width via bisection. This is accomplished by applying a first bipartite stimulation current that bifurcates the initial segment (ie, forms its midpoint). When this first bisection stimulation current is mobilized, the segment is contracted to the lower half of the initial segment. If this first bisection stimulation current is not mobilized, the section is contracted to the upper half of the initial section. This process continues for each successive segment until I _thresh is segmented by the stimulation current to separate by a predetermined width. Once I _{thresh for a} particular stimulation channel is determined, the stimulation intensity is set as a value that is 20% greater than the detected threshold. This is repeated for each stimulation channel until an optimal stimulation signal is set for each. For each stimulation channel, the optimal stimulation signal can be determined sequentially or simultaneously (by proceeding in a similar manner to the multi-channel threshold detection algorithm described below). The determined stimulus value is then preferably used throughout the monitoring procedure.

A threshold search algorithm for optimizing SSEP stimulation parameters is further described with reference to FIGS. FIG. 40 illustrates how the stimulus intensity algorithm quickly searches for the optimal stimulus parameter (in the form of a flowchart). The algorithm first uses polarity A to stimulate at the initial stimulus intensity and determines whether this results in I _recruit (step 411). If the algorithm determines that there is no mobilization, the algorithm reverses the direction of polarity and uses polarity B to stimulate at the same initial stimulus intensity to determine if this results in I _recruit (step 412). ). If the algorithm determines that there is no mobilization, the algorithm moves to step 413 and doubles the stimulus intensity. At step 414, using polarity A, the algorithm stimulates at the second intensity and determines whether this is _Irecruit (step 414). If the answer is no, the algorithm proceeds to step 415, reverses to polarity B, and stimulates at the second intensity. If the answer is still no, step 413 is repeated and the stimulus intensity is doubled again. If at any point during steps 411, 413, 414, or 415, the answer is yes, the algorithm designates this as the initial partition and polarity as shown in step 416 and as described above. . The algorithm then moves to step 417 and the partition is bifurcated. In other words, stimulation at the midpoint of the segment is performed. At step 418, the algorithm bisects the segment until the threshold is known and the stimulus intensity required for the predetermined response is obtained to the desired accuracy. In step 419, the SSEP stimulus intensity is set 20% greater than the detected threshold. As shown in step 420 of FIG. 41, once I _thresh for limb 1 is found, the algorithm begins the second step (step 421) and reflects steps 411-419 to reflect limb 2 Process. This same process is repeated for limb 3 (step 422) and limb 4 (step 423). After the stimulus intensity algorithm has determined the optimal stimulus parameters, SSEP neurophysiological testing can be initiated (step 424).

With reference to FIGS. 27-39, the remaining functions of the neurophysiological monitoring system 10 will be briefly described in detail. In MEP mode, stimulation signals are delivered to the motor cortex via the patient module 14 and the resulting responses are detected from various muscles of the upper and lower limbs. An increase in I _thresh from earlier tests to later tests may indicate a decrease in spinal cord function. Similarly, the absence of a significant EMG response for a given I _stim to a channel that previously reported a significant response to the same or smaller I _stim also indicates a reduction in spinal cord function. These indicators are detected by the system in MEP mode and reported to the surgeon. In automatic MEP mode, the system determines the I _thresh criteria for each channel corresponding to the various monitored muscles, preferably early in the procedure, using the multi-channel algorithm described. _Again , subsequent tests may be performed throughout the procedure to determine the I _thresh for each channel. The difference between the resulting I _thresh value and the corresponding criterion is calculated by the system 10 and compared against the predefined “safe” and “dangerous” difference values. I _thresh , baseline, and difference values are displayed to the user on display 34, along with any other determined safety level indications (red, yellow, green code, etc.) as illustrated in FIG. The In manual MEP mode, the user selects the stimulation current level and the system reports whether the stimulation signal elicits a significant response on each channel. The stimulation results may be shown on the display 34 in the form of “yes” and “no” responses or other equivalent displays, as depicted in FIG. Thus, the surgeon can use either mode to be alerted to possible complications of the spinal cord and take any corrective action deemed necessary at the surgeon's direction.

  The nerve monitoring system 10 is contained within an applicable electrode harness and is directly connected to the spinal nerve via a stimulation electrode 22 placed on the skin over the nerve or using a surgical aid such as the probe 116. The neuromuscular pathway (NMP) via the spasm test mode by electrically stimulating the peripheral nerves (preferably the radial nerve in the lumbar and thoracolumbar applications and the median nerve in the cervical application) Conduct an evaluation. From muscles innervated by the stimulated nerve, evoked responses are detected and recorded, and the results are analyzed to identify the relationship between at least two responses or between the stimulus signal and the response. The identified relationship provides an indication of the current state of the NMP. Relationships identified include, but are not necessarily limited to, one or more of the magnitude ratio between multiple evoked responses and the presence or absence of evoked responses to a given stimulus signal (s). Not. Referring to FIG. 29, via the GUI display 34, the details of the test showing the status of NMP and the relative safety in continuing the neurological test are communicated to the surgeon. Data specific to the function is displayed in the central result area 201 on the monitoring screen 200 used by the various functions implemented by the system 10. The results can be shown as a numerical value 210, as a highlighted label corresponding to the electrode label 86, or as a bar graph of stimulation results (only for the spasm test). On one side of the central result area 201 is a collapsible device menu 202. The device menu displays a graphical representation of each device connected to the patient module 14. On the opposite side of the device menu 202 is a shrinkable test menu 204. The test menu 204 can be used to highlight each test that is available under an operational configuration profile and to navigate between functions. The collapsible stimulus bar 206 indicates the current stimulus state and provides a stimulus start button and a stimulus stop button (not shown) for activating and controlling the stimulus. The collapsible event bar 208 stores all stimulation test results acquired throughout the procedure. Clicking on a specific event opens a note box where you can enter notes for later inclusion in the treatment report and save them with the response. Event bar 208 also includes a chat box mechanism when system 10 is connected to a remote monitoring system, as described above. In the result area 202, results specific to the spasm test can be displayed.

  While FIG. 29 depicts the monitoring screen 200 while the selected function is a spasm test, it should be understood that the mechanism of the monitoring screen 200 applies equally to all functions. Data specific to the result is displayed in the central result area 201. A large saturated color value (not shown) is used to indicate the threshold result. Three different options are provided for indicating the stimulus response level. First, the user can see the waveform. Second, the similarity of the color-coded electrode harness label 86 can be shown on the display. Third, a color-coded label 212 can be integrated with the body image. On one side of the central result area 201 is a reducible device menu 202. The device menu displays a graphical representation of each device connected to the patient module 14. If a device is selected from the device menu 202, an impedance test may be initiated. On the opposite side of the device menu 202 is a shrinkable test menu 204. The test menu 204 can be used to highlight each test that is available under an operational settings profile and to navigate between functions. The collapsible stimulus bar 206 indicates the current stimulus state and provides a stimulus start button and a stimulus stop button (not shown) for activating and controlling the stimulus. The collapsible event bar 208 stores all stimulus test results acquired throughout the procedure so that the user can view the entire case history from the monitoring screen. Clicking on a specific event will open a note box that will later be entered with annotations to include in the treatment report that sequentially records all nerve monitoring functions performed during the procedure as well as the results of the nerve monitoring. Can be saved. In one embodiment, the report can be printed immediately from one or more printers located in the operating room, or, by way of example only, known in the prior art such as floppy disks and / or USB memory sticks Can be copied to any of a variety of memory devices. The system 10 can generate either a complete report or a summary report depending on the specific needs of the user. In one embodiment, the identifiers used to identify the patient module's surgical aids can also be encoded to identify their lot number or other identifying information. Once the auxiliary device is identified, a lot number can be automatically added to the report. Alternatively, a hand-held scanner may be provided and linked to the control unit 12 or patient module 14. Auxiliary packaging is scanned, and in this case as well, information can be routed directly to treatment reports. The event bar 208 also includes a chat box mechanism so that when the system 10 is connected to a remote monitoring system, users within the operating room can communicate simultaneously with an individual performing related nerve monitoring at a remote location.

The nerve monitoring system 10 tests the integrity of the pedicle holes (during and / or after formation) and / or screws (during and / or after introduction) via basal stimulation EMG and dynamic stimulation EMG tests. be able to. To perform a basic stimulus EMG, the test probe 116 is placed in the screw hole prior to screw insertion or placed over the head of the inserted screw and the stimulus signal is applied. The insulating properties of the bone prevent the stimulation current from communicating with the nerve to a certain amplitude, thus resulting in a relatively high I _thresh as determined through the basic threshold search algorithm described below. However, when the stalk wall is cut by a screw or tap, the current density in the cut zone increases to the point where the stimulation current passes to the adjacent nerve root, which depolarizes at a lower stimulation current. Therefore, I _thresh is relatively low. The system described herein uses this knowledge to inform the practitioner of the current I _thresh of the screw being tested and to determine if a pilot hole or screw has cut through the pedicle wall. Can be used.

  In the dynamic stimulation EMG mode, the test probe 116 can be replaced with a clip 18 that can be utilized to couple a surgical tool, such as, for example, the tap member 28 or the pedicle access needle 26 to the nerve monitoring system 10. . Thus, while the tool is in use, the stimulation signal can pass through the surgical tool to perform a pedicle integrity test. Thus, testing can be performed during pilot hole preparation by connecting the access needle 26 to the nerve monitoring system 10, during pilot hole formation, and by connecting the tap 28 to the system 10. Similarly, integrity tests can be performed during screw introduction by connecting the pedicle screws to the nerve monitoring system 10 (such as via pedicle screw instruments).

  In both basal stimulation EMG mode and dynamic stimulation EMG mode, the signal characteristics used for testing in the lumbar test are the proximity of the spinal cord to the thoracic and cervical pedicles when monitoring within the thoracic and / or cervical level. Therefore, it may not be effective. Ruptures formed in the lumbar spine pedicles result in stimulation being applied to the nerve roots, while cuts in the thoracic or cervical pedicles may instead result in irritation of the spinal cord. Yes, but the spinal cord may not respond to stimulation signals in the same way as nerve roots. To account for this, the surgical system 10 has the ability to deliver stimulation signals having different characteristics based on the region selected. By way of example only, when a lumbar region is selected, the stimulus signal in the stimulus EMG mode comprises a single pulse signal. On the other hand, when the chest and neck regions are selected, the stimulation signal can be configured as a multiple pulse signal.

Stimulus results (including but not necessarily limited to at least one of a numerical I _thresh value and a color-coded safety level indication) and other relevant data are illustrated in FIGS. At least communicated to the user on the main display 34. FIG. 29 illustrates a monitoring screen 200 where the basal stimulus EMG test has been selected. FIG. 30 illustrates a monitoring screen 200 where the dynamic stimulus EMG test has been selected. In one embodiment of various screw test functions (eg, basal and dynamic), green corresponds to a threshold range above 10 milliamps (mA), yellow corresponds to a stimulation threshold range of 7-10 mA, and red Corresponds to a stimulation threshold range of 6 mA or less. An EMG channel tab can be selected via the touch screen display 26 to show the corresponding neural I _thresh . In addition, EMG channels that process the lowest I _thresh can be automatically highlighted and / or colored to clearly show this fact to the user.

The nerve monitoring system 10 can perform a nerve proximity test via the XLIF mode to ensure safe and reproducible access to the surgical target site. Using surgical access components 26-32, system 10 passes through any of a variety of tissues having neural structures that, when contacted or compromised, can result in neurological dysfunction in the patient. The presence of neural structures is detected before, during and after the establishment of the surgical path (or through it). The surgical access components 26-32 are designed to bluntly dissect tissue between the patient's skin and the surgical target site. A dilator of increasing diameter, including one or more stimulation electrodes, is advanced toward the target site until a sufficient surgical path is established to advance the retractor 32 to the target site. As the dilator advances to the target site, an electrical stimulation signal is emitted through the stimulation electrode. The stimulation signal stimulates the nerve adjacent to the stimulation electrode and the corresponding EMG response is monitored. As the nerve gets closer to the stimulation electrode, the resistance due to human tissue decreases, so the stimulation current required to elicit a muscle response is reduced and less current is required to depolarize the nerve tissue . Using the basic threshold search algorithm described below, I _thresh is calculated, providing a means of communication between the stimulus signal and the nerve, thus providing a proximity related indication between the access component and the nerve. The An example of a monitoring screen 200 in which the XLIF mode is enabled is depicted in FIG. In a preferred embodiment, the green or safety level corresponds to a stimulation threshold range of 10 milliamps (mA) or higher, the yellow level indicates a stimulation threshold range of 5-9 mA, and the red level has a stimulation threshold range of 4 mA or lower. Show.

  The nerve monitoring system 10 can also perform continuous EMG monitoring while the system is in any of the above-described modes. Continuous EMG monitoring continuously listens to spontaneous muscle activity, which can indicate a potential risk. The system 10 can automatically cycle to continuous monitoring after a pause of 5 seconds (as an example only). By initiating the stimulus signal in the selected mode, the duration monitoring is suspended until the system 10 is rested again for 5 seconds, and the duration resumes when the system 10 is rested again for 5 seconds. An example of a monitoring screen 200 with persistent EMG enabled is depicted in FIG.

  The nerve monitoring system 10 can also implement a navigation guidance function. The navigation guidance mechanism ensures safe and reproducible pedicle screw placement by monitoring the axial trajectory of the surgical instrument used during pilot hole formation and / or screw insertion, by way of example only Can be used for. Preferably, EMG monitoring may be performed simultaneously with the navigation guidance mechanism. An angle measurement device (hereinafter “tilt sensor”) 54 is connected to the patient module 14 via one of the auxiliary ports 62 to perform navigation guidance. The tilt sensor measures its angular orientation with respect to a reference axis (eg “vertical” or “gravity” etc.) and the control unit displays the measured value. Because the tilt sensor is attached to a surgical instrument, the angular orientation of the instrument can also be determined, allowing the surgeon to position and maintain the instrument along a desired trajectory during use. In general, during pilot hole formation, in order to orient and maintain the surgical instrument along the desired trajectory, the surgical instrument is advanced into the pedicles while being oriented at the zero angular position (optional Open, small open, or percutaneous access). The instrument is then angled in the sagittal plane until the proper head-tail angle is reached. Maintaining the proper head-to-tail angle, the surgical instrument may be angled in the cross-section until a suitable medial-lateral angle is reached. Once the control unit 12 indicates that both the medial-lateral angle and the head-tail angle have been correctly adapted, the instrument may be advanced into the pedicle to form a pilot hole, Monitor the angular trajectory of the instrument until completion.

  The control unit 12 can communicate any numerical values, diagrams, and audio feedback corresponding to the orientation of the tilt sensor in the sagittal plane (head-to-tail angle) and in the cross-section (inside-outside angle). The medial-lateral and head-tail angle readings may be displayed simultaneously and continuously while the tilt sensor is in use, or any other variation thereof (eg, individually and / or intermittently). . FIG. 34 illustrates, by way of example only, one embodiment of a GUI screen for a navigation guidance function. The angular orientation of the instrument is displayed with a color-coded target scheme to help the user find the desired angle.

In order to obtain I _thresh and utilize the useful information it provides, the system 10 identifies the peak-to-peak voltage (V _pp ) of each EMG response corresponding to a given stimulation current (I _Stim ), taking measurement. It may be difficult to identify the true V _{pp of the} response due to the presence of stimuli and / or noise artifacts that can lead to false V _pp measurements. In order to overcome this challenge, the neuromonitoring system 10 of the present invention is a jointly owned and commonly assigned name “System and Methods for Performing Dynamic Integrity Assessment”, referred to above, August 8, 2004. Any number of suitable artifact removal techniques, such as those fully shown and described in PCT Application No. PCT / US2004 / 025550, filed on May 5, may be employed, the entire content of which is Which is incorporated by reference into the present disclosure as if fully set forth herein. Upon measuring the V _{pp of} each EMG response, the V _pp information is analyzed with respect to the corresponding stimulation current (I _stim ) to identify the minimum stimulation current (I _Thresh ) that can result in a predetermined V _pp EMG response. The According to the present invention, the determination of I _Thresh can be accomplished via any of a variety of suitable algorithms or techniques.

FIGS. 35A-D, by way of example only, illustrate the principles of the threshold search algorithm of the present invention used to quickly find I _thresh . The method for finding I _thresh utilizes a segmentation method and a _bisection method. The segmentation method quickly finds the range (segment) of stimulation currents that should contain I _thresh, and the _bisection method narrows the segment until I _thresh is known within the specified accuracy. If the channel stimulation current threshold I _thresh exceeds the maximum stimulation current, the threshold is considered out of range.

35A-D illustrate the partitioning mechanism of the threshold search algorithm of the present invention. Stimulation begins with a minimal stimulation current, such as 1 mA (as an example only). The associated current value depends, in part, on the function being performed (eg, high current is used for MEP and generally low current is used for other functions) and is described herein. It will be appreciated that the current values are for illustration only and may actually be adjusted to any scale. The level of each subsequent stimulus is doubled from the previous stimulus level until the stimulation current is mobilized (ie, produces an EMG response with a V _pp greater than or equal to V _thresh ). The first stimulation current to mobilize (8 mA in FIG. 35B) forms the initial segment with the last stimulation current not mobilized (4 mA in FIG. 35B).

35C-D illustrate the bisection mechanism of the threshold search algorithm of the present invention. After the threshold current I _thresh is segmented (FIG. 35B), the initial segment is progressively reduced to a predetermined width, such as 0.25 mA (by way of example only) via bisection. This is accomplished by applying a first bisection stimulation current (6 mA in FIG. 35C) that bifurcates the initial segment (ie, forms the midpoint of the initial segment). When this first bisection stimulation current is mobilized, the segment is reduced to the lower half of the initial segment (eg, 4 mA to 6 mA in FIG. 35C). If this first bisection stimulation current is not mobilized, the segment is reduced to the upper half of the initial segment (eg, 6 mA to 8 mA in FIG. 35C). This process continues for each successive segment until I _thresh is segmented by the stimulation current to separate by a predetermined width (in this case 0.25 mA). In the present example shown, this can be achieved by applying a second bisection stimulation current (forming the midpoint of the second segment, or 5 mA in this example). Since this second _bisection stimulation current is less than I _thresh , it does not mobilize. In this way, the second section is reduced to its upper half (5 mA to 6 mA) to form the third section. A third bisection stimulation current is then applied that forms the midpoint of the third segment (in this case, 5.50 mA). Since this third _bisection stimulation current is less than I _thresh , it does not mobilize. Thus, the third section is reduced to its upper half (5.50-6 mA) to form the fourth section. A fourth bisection stimulation current is applied that forms the midpoint of the fourth section (in this case 5.75 mA). The fourth _bisection stimulation current mobilizes because it exceeds I _thresh . The final section is 5.50 mA to 5.75 mA. Because of the “response” or mobilization at 5.50 mA and the “no response” or lack of mobilization at 5.75 mA, I _thresh can be inferred to be within this range. In one embodiment, the midpoint of this final partition may be defined as I _thresh , however, any value within the final partition may be selected as I _thresh without departing from the scope of the present invention. Also good. Depending on the enabled mode, the algorithm can stop after finding I _thresh for the first response channel (ie, the channel with the lowest I _thresh ), or to determine each channel's I _thresh On the other hand, the segmentation and bisection steps can be repeated. In one embodiment, multi-channel I _thresh determination can be accomplished by employing additional steps of the multi-channel threshold detection algorithm described below.

Further, in a “dynamic” functional mode, including but not necessarily limited to dynamic stimulation EMG and XLIF, the system can continuously update the stimulation threshold level and indicate that level to the user. To do so, the threshold search algorithm does not repeatedly determine the I _thresh level, but rather determines whether the stimulation current threshold is changing. This is accomplished by monitoring the steps involved in switching between stimuli at the lower end of the final segment and stimuli at the upper end, as illustrated in FIG. 35D. If the threshold has not changed, the lower end stimulation current of the segment should not elicit a response, while the upper end stimulation current of the segment should elicit a response. If any of these conditions are not met, the category is adjusted accordingly. The process is repeated for each valid channel to continue to ensure that each threshold is partitioned. If the stimulus fails three consecutive times to elicit the expected response, then the algorithm returns to the segmentation phase to re-establish the segment. In the event that a change in I _thresh is detected during the monitoring phase, the user can be immediately alerted via screen display and / or audio feedback. By way of example only, immediately after a change in I _thresh is detected, but before a new I _thresh value is determined, the color shown on the display corresponding to the previous I _thresh is neutral (e.g., black, Gray). If a voice sound is used to represent a particular safety level, the sound may be stopped as soon as a change is detected. Once a new I _thresh value is determined, the color and / or audio sound can be changed again to represent the value.

In an alternative embodiment, rather than starting by entering the segmentation phase with minimal stimulation current and segmenting upwards until I _thresh is segmented, the threshold search algorithm immediately sets the appropriate safety level. You may start with a decision and then enter a segmentation phase. The algorithm can accomplish this by initiating stimulation at one or more of the boundary current levels. By way of example only and with reference to FIG. 36, the algorithm can begin by delivering a stimulus signal at the boundary between a danger level (eg, red) and an attention level (eg, yellow). If the safety level is not apparent after the first stimulus, the algorithm can be stimulated again at the boundary between the attention level (eg, yellow) and the safety level (eg, green). Once the safety level is known (ie after the first stimulus if the safety level is red, or after the second stimulus if the safety level is yellow or green), the screen display is suitable It may be updated to color and / or an encoded audio signal may be emitted. As the screen display is updated, the algorithm can enter a segmentation and _bisection stage to determine the actual I _thresh value. When the I _thresh value is determined, the display can be updated again to reflect the additional information. In the dynamic mode, if the monitoring phase detects a change in I _thresh , the algorithm may optionally select a boundary level (single or singular) before entering the segmentation and _bisection phase to determine a new I _thresh. Re-stimulate and update the color and / or audio signal.

For some functions, such as MEP (as an example), it may be desirable to obtain I _thresh for each valid channel each time the function is performed. This is to evaluate the change in I _thresh over time as a means for detecting potential problems (such as detecting I _thresh below a predetermined level determined to be safe, such as in the stimulus EMG mode) Is particularly advantageous). As described above, an algorithm can be used to find the I _thresh for each valid channel, which requires a potentially large number of stimuli, each associated with a particular time delay. , May significantly increase response time. When performed repeatedly, this can also significantly increase the total time required to complete the surgical procedure, which can result in additional risk and cost to the patient. In order to overcome this drawback, the preferred embodiment of the _{neuromonitoring} system 10 quickly determines the I _thresh of each channel while minimizing the number of stimuli and thus necessary to perform such a determination. A multi-channel threshold search algorithm to reduce the time taken to

The multi-channel threshold search algorithm reduces the number of stimuli required to complete the segmentation and _bisection steps when multi-channel I _thresh is discovered. The multi-channel algorithm does so by omitting stimuli whose results are predictable from already acquired data. When the stimulus signal is omitted, the algorithm proceeds as if the stimulus had been performed. However, instead of reporting the actual mobilization results, the reported results are inferred from previous data. This allows the algorithm to proceed immediately to the next step without the time delay associated with the stimulus signal.

Regardless of which channel's I _thresh is being processed, each stimulus signal elicits a response from all valid channels. That is, any channel will or will not mobilize in response to the stimulus signal (again, the channel will have an EMG response that the stimulus signal is deemed meaningful for that channel, such as V _{pp of} about 100 μV. If triggered, it is likely mobilized). These mobilization results for each channel are recorded and stored. Later, when the I _thresh for different channels is processed, the stored data can be accessed, and based on that data, the algorithm omits the stimulation signal and whether the channel is mobilized at a given stimulation current. I can guess.

There are two reasons why the algorithm can omit the stimulus signal and report previous mobilization results. The stimulation signal can be omitted if the selected stimulation current is a repeat of the previous stimulation. If by way of example only, in order to determine one of the channels of the _{I thresh,} applies a 1mA stimulation current, to determine the _{I thresh} another channel, that is later required stimulation with 1mA, The algorithm can omit the stimulus and report previous results. If the specific stimulation current required has not been used before, the stimulation signal can still be omitted if the results are already clear from previous data. By way of example only, if a 2 mA stimulation current is applied to determine I _thresh for the previous channel, and the current channel is not mobilized, a 1 mA stimulation will be used later to determine I _thresh for the current channel. When needed, the algorithm can infer from previous stimuli that the current channel did not mobilize at 1 mA because it did not mobilize at 2 mA. Thus, the algorithm can omit the stimulus and report previous results.

FIG. 37 illustrates a method (in flowchart form) where the multi-channel threshold search algorithm determines whether to stimulate or not to stimulate and just report previous results. The algorithm first determines whether the selected stimulation current is already in use (step 302). If the stimulation current is being used, the stimulation is omitted and the previous stimulation result for the current channel is reported (step 304). If the stimulation current is not being used, the algorithm determines _{I recruit} the current channel (Step 306) and _{I Norecruit} (step 308). I _recruit is the lowest stimulation current mobilized on the current channel. I _norecruit is the highest stimulation current that could not be mobilized on the current channel. Next, the algorithm determines whether I _recruit is greater than I _norecruit (step 310). An I _recruit not _greater than I _norecruit indicates that a change has occurred in I _thresh on the channel. Thus, previous results may not reflect current threshold conditions and the algorithm does not use them to infer responses to a given stimulation current. The algorithm stimulates with the selected current and reports the current channel results (step 312). If I _recruit is greater than _{I Norecruit,} the algorithm determines the stimulation current that is _selected, whether higher than _{I recruit,} whether it is between _I whether lower _Norecruit, or _{I recruit} and _{I Norecruit} ( Step 314). If the selected stimulation current is higher than _Irecruit , the algorithm omits the stimulation and reports that the current channel is mobilized at the specified current (step 316). If the selected stimulation current is lower than I _norecruit , the algorithm _assumes that the current channel is not mobilized at the selected current and reports the result (step 318). If the selected stimulation current is comprised between I _recruit and I _Norecruit, the result of stimulation can not be estimated, the algorithm stimulates at selected current and reports the results of the current channel (Step 312). This method may be repeated until the I _thresh for any valid channel is determined.

For clarity, FIGS. 38A-C illustrate the use of a multi-channel threshold search algorithm to determine I _thresh on two channels. However, the multi-channel algorithm is not limited to just finding I _thresh for two channels; rather, according to a preferred embodiment of the neuromonitoring system 10, any number of channels, such as eight channels (for example) It should be understood that it can be used to discover I _thresh . Referring to FIG. 38A, channel 1 has I _thresh found to be 6.25 mA and channel 2 has I _thresh found to be 4.25 mA. Channel 1 I _thresh is first discovered using the segmentation and _bisection method described above, as illustrated in FIG. 38B. Segmentation begins with a minimum stimulation current of 1 mA (for illustrative purposes only). Since this is the first channel to be processed and there is no previous mobilization result, no stimulation is omitted. The stimulation current is doubled for each sequential stimulation until a significant EMG response is induced at 8 mA. The initial section of 4-8 mA is contained within the final section using the bisection method described above, with the stimulation threshold I _thresh separated by the selected width or resolution (again, 25 mA in this case). Until it is divided into two. In this example, the final segment is 6 mA to 6.25 mA. I _thresh may be defined as any point in the final partition, or as the midpoint of the final partition (in this case 6.125 mA). In either event, I _thresh is selected and reported as channel 1 I _thresh .

Once channel 1's I _thresh is found, the algorithm begins with channel 2 as illustrated in FIG. 38C. Again, the algorithm starts processing channel 2 by determining the initial partition, which is 4-8 mA again. All the stimulation currents required in the segmentation phase are used in the determination of channel 1 I _thresh . The algorithm refers back to the stored data to determine how channel 1 responded to the previous stimulus. From the stored data, the algorithm can deduce that channel 2 does not mobilize at 1, 2, and 4 mA stimulation current, but mobilizes at 8 mA. These stimuli are omitted and the inferred results are displayed. The first bipartite stimulation current selected in the bisection process (6 mA in this case) has been used previously, so the algorithm omits the stimulation and urges channel 2 to mobilize at that stimulation current. Can be reported. The selected next bisection stimulation current (in this case 5 mA) has not been used before, so the algorithm must determine whether the result of the stimulation at 5 mA can still be inferred. In the example shown, I _recruit and I _norecruit are determined to be 6 mA and 4 mA, respectively. 5mA _Since comprised between _{I recruit} and _{I Norecruit,} the algorithm can not infer the results from previous data, Thus, stimulation can not be omitted. The algorithm then stimulates with 5 mA and reports that the channel is mobilized. The section is reduced to the lower half (the next bisection stimulation current is 4.50 mA). The 4.5 mA stimulation current has not been used previously, so the algorithm again determines I _recruit and I _norecruit (in this case 5 mA and 4 mA). Selected stimulation current (4.5 mA) _is comprised between _{I recruit} and _{I Norecruit,} Therefore, the algorithm stimulates at 4.5 mA, report the results. Here, the section is its final width of 25 mA (for illustrative purposes only). I _thresh may be defined as any point in the final partition, or as the midpoint of the final partition (in this case, 4.125 mA). In either event, I _thresh is selected and reported as channel 2 I _thresh .

Although the multi-channel threshold search algorithm is described above to process the channels in numerical order, it is understood that the actual order in which the channels are processed is not important. The channel processing order may be biased (described below) to provide the highest or lowest threshold first, or any processing order may be used. It is further understood that the algorithm does not necessarily have to be completed for one channel before starting the processing of the next channel, provided that the intermediate state of the algorithm is maintained for each channel. Channels are still processed one at a time. However, the algorithm can cycle between one or more channels and processes as little stimulation current as that channel before moving to the next channel. By way of example only, the algorithm can be stimulated at 10 mA while processing I _thresh for the first channel. Prior to stimulation with 20 mA (the next stimulation current in the segmentation phase), the algorithm can cycle to any other channel and process it with 10 mA stimulation current (omitting stimulation if applicable) To do). Any or all of the channels may be processed in this manner before returning to the first channel to apply the next stimulus. Similarly, the algorithm need not return to the first channel to stimulate at 20 mA, but can instead select a different channel to process first at the 20 mA level. In this way, the algorithm can be biased in order to advance all channels essentially together and find the lower threshold channel first or the upper threshold channel first. By way of example only, the algorithm can stimulate at one current level and process each channel in turn at that level before proceeding to the next stimulation current level. The algorithm can continue in this pattern until the channel with the lowest I _thresh is partitioned. The algorithm then processes the channel exclusively until I _thresh is determined, then the other with one stimulus current level at a time until the channel with the next lowest I _thresh is partitioned. You can return to processing the channel. This process may be repeated until the I _thresh for each channel is determined in the order of lowest to highest I _thresh . If I _{thresh of} more than one channel is included in the same partition, the partition may be bifurcated and _iterates through each channel in the partition until it is clear which has the lowest I _thresh To do. If it is more advantageous to first determine the highest I _thresh , the algorithm can continue the partitioning phase until a partition of every channel is found, and then bifurcate each channel in descending order.

FIGS. 39A-B advantageously provide the ability to further reduce the number of stimuli required to find I _thresh when the I _thresh value for a particular channel has been previously determined. Figure 2 illustrates a further mechanism of the threshold search algorithm. In the event that there is a previous I _thresh determination for a particular channel, the algorithm can start by simply checking the previous I _thresh rather than starting again with the segmentation and _bisection method. The algorithm first determines whether an initial threshold decision for the channel is being made, or if there is a previous I _thresh decision (step 320). If it is not an initial decision, the algorithm confirms the previous decision, as described below (step 322). If the previous threshold is confirmed, the algorithm reports its value as the current I _thresh (step 324). If it is an initial I _thresh determination, or if the previous threshold cannot be confirmed, the algorithm determines the I _thresh and reports the value, a segmentation function (step 326) and a bisection function (step 328). ) Is performed (step 324).

Although the search algorithm is described in terms of finding I _thresh (the lowest stimulation current that elicits a pre-determined EMG response), alternative stimulation thresholds may be useful in assessing spinal health or in neural monitoring functions, It is contemplated that it can be determined by a search algorithm. By way of example only, a search algorithm may be employed by the system 10 to determine the stimulation voltage threshold Vstim _thresh . This is the lowest stimulation voltage (as _opposed to the lowest stimulation current) required to induce a significant EMG response V _thresh . The segmentation, bisection, and monitoring states are performed as described above for each valid channel, using a voltage-based segmentation instead of the current-based segmentation described above. Further, although described above in the context of MEP monitoring, the algorithms described herein also include, but are not limited to, pedicle integrity (screw test), nerve detection, and nerve root incision. It is understood that it can also be used to determine the stimulation threshold (current or voltage) of any other EMG related function.

  Although the invention has been described with reference to the best mode for accomplishing the objects of the invention, modifications can be achieved without departing from the spirit or scope of the invention in light of these teachings. Will be understood by those skilled in the art. For example, the present invention may be implemented using any combination of computer programming software, firmware, or hardware. As a preparatory step for practicing the present invention or constructing a device according to the present invention, the computer programming code according to the present invention (whether software or firmware) is typically fixed (hard). It can be stored in one or more machine-readable storage media such as semiconductor memory such as a drive, diskette, optical disk, magnetic tape, ROM, PROM, etc., thereby producing a product according to the invention. A product containing computer programming code can be used to execute code directly from a storage device, by copying the code from a storage device to another storage device such as a hard disk, RAM, or for remote execution. Used by transmitting above. As one skilled in the art can envision, many different combinations of the above can be used, and thus the invention is not limited to the scope specified.

Claims (14)

A system for performing somatosensory evoked potential monitoring during surgery,
A stimulator configured to deliver electrical stimulation signals to a patient's peripheral nerves;
At least one sensor configured to detect a somatosensory response elicited by the electrical stimulation signal;
A control unit in communication with the stimulator and the sensor,
(A) instructing transmission of the stimulation signal;
(B) receiving the induced somatosensory response data from the sensor;
(C) assessing spinal health by identifying a relationship between the somatosensory response to a first stimulus signal and a subsequent somatosensory response to a second stimulus signal;
(D) communicating the evaluation to the user;
A control unit configured as
A system comprising: The system of claim 1, wherein the rating is communicated by displaying a color associated with the rating. The system of claim 2, wherein the displayed color is one of green, yellow, and red. The relationship identified is at least one of a change in latency and a change in amplitude between the first somatosensory response and the subsequent somatosensory response. The surgical operation system in any one of -3. The system according to any of claims 1 to 4, wherein the control unit is configured to direct transmission of stimulation signals to at least four different stimulation sites and to identify the relationship of each stimulation site. . The system according to claim 1, wherein the control unit is configured to receive instructions from a user to modify at least one parameter associated with the stimulation signal. The system of claim 6, wherein at least one of pulse number, pulse width, pulse rate, and pulse current level can be modified. The system of claim 7, wherein the control unit is configured to automatically optimize the stimulation signal parameters. The system of claim 8, wherein the control unit implements a threshold search algorithm to optimize the stimulus signal. The system of claim 9, wherein the threshold search algorithm is based on successive approximation. The successive approximation is
(A) establishing a bracket in which the lowest stimulation current is contained;
(B) sequentially bisecting the bracket until the minimum stimulation current is determined within a specified accuracy;
The system of claim 10, comprising: 12. A system according to any preceding claim, further comprising a display for communicating visually with the user in communication with the control unit. The system of claim 12, wherein the display includes a touch screen control function that allows a user to interface with the control unit. The system according to claim 1, wherein the control unit is further configured to perform at least one of a stimulation EMG evaluation and a MEP evaluation.

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